WO2009013692A2 - Milieu d'adaptation multimodal pour des mesures par tomographie optique diffuse et ultrasons - Google Patents

Milieu d'adaptation multimodal pour des mesures par tomographie optique diffuse et ultrasons Download PDF

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Publication number
WO2009013692A2
WO2009013692A2 PCT/IB2008/052910 IB2008052910W WO2009013692A2 WO 2009013692 A2 WO2009013692 A2 WO 2009013692A2 IB 2008052910 W IB2008052910 W IB 2008052910W WO 2009013692 A2 WO2009013692 A2 WO 2009013692A2
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Prior art keywords
medium
matching medium
matching
optical
turbid
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WO2009013692A3 (fr
Inventor
Martinus B Van Der Mark
Robert R. Entrekin
Michael C. Van Beek
Levinus P. Bakker
Nijs C. Van Der Vaart
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Koninklijke Philips NV
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Koninklijke Philips Electronics NV
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K49/00—Preparations for testing in vivo
    • A61K49/0002—General or multifunctional contrast agents, e.g. chelated agents
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
    • A61B5/0091—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for mammography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/43—Detecting, measuring or recording for evaluating the reproductive systems
    • A61B5/4306—Detecting, measuring or recording for evaluating the reproductive systems for evaluating the female reproductive systems, e.g. gynaecological evaluations
    • A61B5/4312—Breast evaluation or disorder diagnosis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/08—Clinical applications
    • A61B8/0825—Clinical applications for diagnosis of the breast, e.g. mammography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/42—Details of probe positioning or probe attachment to the patient
    • A61B8/4272—Details of probe positioning or probe attachment to the patient involving the acoustic interface between the transducer and the tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/42—Details of probe positioning or probe attachment to the patient
    • A61B8/4272—Details of probe positioning or probe attachment to the patient involving the acoustic interface between the transducer and the tissue
    • A61B8/429—Details of probe positioning or probe attachment to the patient involving the acoustic interface between the transducer and the tissue characterised by determining or monitoring the contact between the transducer and the tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4416—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device related to combined acquisition of different diagnostic modalities, e.g. combination of ultrasound and X-ray acquisitions
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K49/00—Preparations for testing in vivo
    • A61K49/22—Echographic preparations; Ultrasonic imaging preparations
    • A61K49/222—Echographic preparations; Ultrasonic imaging preparations characterised by a special physical form, e.g. emulsions, liposomes
    • A61K49/226—Solutes, emulsions, suspensions, dispersions, semi-solid forms, e.g. hydrogels
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/14—Coupling media or elements to improve sensor contact with skin or tissue
    • A61B2562/146—Coupling media or elements to improve sensor contact with skin or tissue for optical coupling
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0033—Features or image-related aspects of imaging apparatus, e.g. for MRI, optical tomography or impedance tomography apparatus; Arrangements of imaging apparatus in a room
    • A61B5/0035—Features or image-related aspects of imaging apparatus, e.g. for MRI, optical tomography or impedance tomography apparatus; Arrangements of imaging apparatus in a room adapted for acquisition of images from more than one imaging mode, e.g. combining MRI and optical tomography

Definitions

  • Multimodality matching medium for diffuse optical tomography and ultrasound measurements
  • the invention relates to a matching medium for conducting optical energy generated by a light source at least from the light source to an optically turbid medium (hereinafter turbid medium) to be irradiated with optical energy generated by the light source.
  • turbid medium optically turbid medium
  • the invention also relates to a system for imaging an interior of a turbid medium comprising: a light source for generating optical energy to be coupled into the turbid medium; an ultrasound source for generating ultrasound energy to be coupled into the turbid medium.
  • the invention also relates to a medical image acquisition system comprising: a light source for generating optical energy to be coupled into the turbid medium; an ultrasound source for generating ultrasound energy to be coupled into the turbid medium.
  • the invention also relates to a method of imaging an interior of a turbid medium comprising the following steps: coupling optical energy from a light source into the turbid medium; coupling ultrasound energy from an ultrasound source into the turbid medium.
  • the invention also relates to a method for obtaining a multimodality matching medium.
  • An optical matching medium for conducting optical energy generated by a light source at least from the light source to a turbid medium to be irradiated with at least a part of the optical energy generated by the light source is known from US patent 5,907,406.
  • the known optical matching medium can be used for imaging an interior of a turbid medium, such as biological tissue, using diffuse optical tomography.
  • the matching medium may be used, for instance, for imaging an interior of a female breast.
  • at least a part of the turbid medium, in this case a female breast may be accommodated in a receiving volume.
  • the receiving volume is bounded by a cuplike wall portion. However, this is not always necessary.
  • the part of the turbid medium under investigation is surrounded by the matching medium.
  • Light from a light source is coupled into the receiving volume and into the turbid medium.
  • the light is chosen such that it is capable of propagating through the turbid medium.
  • For imaging an interior of a female breast light having a wavelength within a range of 400 nm to 1400 nm is typically used.
  • Scattered light emanating from the turbid medium as a result of coupling light into the receiving volume is coupled out of the receiving volume.
  • Light coupled out of the receiving volume is used to reconstruct an image of an interior of the turbid medium.
  • the matching medium is chosen such that the optical parameters of the matching medium, such as the absorption and scattering coefficients, are substantially identical to the corresponding optical parameters of the turbid medium. In this way, image artefacts resulting from optical boundary effects that occur when light is coupled into and out of the turbid medium can be reduced. Furthermore, use of the matching medium prevents the occurrence of an optical short-circuit in the receiving volume around the turbid medium. An optical short-circuit occurs when light is detected that has propagated along a path inside the receiving volume but outside the turbid medium and, as a consequence, has not been sufficiently scattered and attenuated.
  • the intensity of the insufficiently scattered and attenuated detected light may dwarf the intensity of detected light that has been scattered and attenuated through passage through the turbid medium.
  • ultrasound energy is coupled into and out of the receiving volume comprising the turbid medium.
  • the ultrasound energy coupled out of the receiving volume would then be used to reconstruct an image of an interior of the turbid medium. It is a characteristic of the procedure involving the known matching medium described above that it is hard to acoustically couple the turbid medium to its surroundings efficiently.
  • this object is realized in that a matching medium is provided for conducting optical energy generated by a light source at least from the light source to a turbid medium to be irradiated with optical energy generated by the light source and for conducting ultrasound energy generated by an ultrasound source at least from the ultrasound source to the turbid medium to be irradiated with ultrasound energy generated by the ultrasound source with the matching medium having optical and ultrasound characteristics that substantially match the corresponding optical and ultrasound characteristics of the turbid medium.
  • a multimodality matching medium is suitable for both optical and acoustic coupling of human tissue, such as a female breast, to its surroundings enabling multimodality measurements of human tissue.
  • An acoustic speed of sound between 1500 m per second and 1580 m per second is useful for, for instance, imaging non-skin human tissue as the speed of sound in such human tissue is about 1540 m per second, which is in the middle of the aforementioned range.
  • a speed of sound between 1580 m per second and 1680 m per second is useful for, for instance, imaging human skin or skin covered human tissue for which ultrasound waves have to pass through skin first in order to reach the tissue.
  • Human skin has a speed of sound of about 1610-1640 m per second, which is inside the above-mentioned range.
  • This embodiment has the advantage that a matching medium according to this embodiment can be used in direct contact with human skin. This is beneficial if, for instance, the matching medium is used in imaging an interior of a female breast. If a matching medium is not suitable for use in direct contact with human skin extra measures, such as placing a flexible membrane between the matching medium and the skin, are required which are not required with a matching medium according to this embodiment. Moreover, a matching medium that is suitable for use in direct contact with human skin is also beneficial for the general handling of the medium.
  • This embodiment has the advantage that a matching medium according to this embodiment absorbs less optical energy than a matching medium according to the previous embodiment, increasing the amount of optical energy emanating from the receiving volume during a measurement and hence enabling stronger detector signals to be obtained from the receiving volume.
  • This embodiment has the advantage that a matching medium according to this embodiment absorbs less optical energy than a matching medium according to the previous embodiment, increasing the amount of optical energy emanating from the receiving volume during a measurement and hence enabling stronger detector signals to be obtained from the receiving volume.
  • a multimodality matching medium may be a fluid as fluids have the advantage of being easy to accommodate in and removed from the receiving volume intended to receive the turbid medium of interest.
  • the fluid may comprise or capture gas bubbles because of handling of the fluid without the gas bubbles being able to escape from the fluid on a timescale acceptable for measurements involving, for instance, a female breast.
  • Gas bubbles in the matching medium are undesirable for several reasons. First of all, gas bubbles in the matching medium would lead to reflections of ultrasound waves propagating through the medium while examining a turbid medium. Second, gas bubbles might also interfere with the propagation of optical energy through the matching medium.
  • this embodiment has the advantage that the value of the viscosity of the fluidic multimodality matching medium according to the invention is capped at a value such that in the event the fluid comprises gas bubbles these bubbles can escape from the matching medium on acceptable timescales. Acceptability is determined by the type of measurement. Longer timescales may be acceptable for the examination of, for instance, inanimate objects, whereas smaller timescales may be required when examining, for instance, a female breast.
  • the matching medium comprises a first component and a second component with the first component being an optical matching medium having optical characteristics that substantially match the corresponding optical characteristics of the turbid medium, with the second component being an acoustic adapter for matching the ultrasound characteristics of the matching medium to the corresponding ultrasound characteristics of the turbid medium, and with the optical characteristics of the matching medium being substantially determined by the optical matching medium.
  • This embodiment has the advantage that it enables adapting an optical matching medium into a multimodality matching medium for both diffuse optical tomography and ultrasound measurements.
  • a number of optical matching mediums already exist. By adding a suitable acoustic adapter to the optical matching medium the ultrasound characteristics of the combination can be made to substantially match the corresponding characteristics of a turbid medium. If the optical properties of the combined matching medium are substantially determined by the optical matching medium, the optical and ultrasound matchings can be carried out relatively independent of each other.
  • the optical matching medium comprises a water-based fluid comprising titanium dioxide particles and at least one dye and in that the acoustic adapter comprises at least one out of the following group: an alcohol, a glycol, a polyol, a polymer.
  • the optical matching medium comprises a water-based fluid comprising titanium dioxide particles and at least one dye and in that the acoustic adapter comprises at least one out of the following group: an alcohol, a glycol, a polyol, a polymer.
  • This embodiment has the advantage that the range of the speed of sound in the matching medium ranges from about 1480 m per second (depending on temperature) to about 1700 m per second. This range includes the speed of sound in, for instance, non-skin human biological tissue, which is about 1540 m per second as well as in human skin, which has a speed of sound of about 1610-1640 m per second.
  • the acoustic adapter comprises glycerin with the glycerin making up between 0 and 20 percent by weight of the matching medium.
  • This embodiment has the advantage that the range of the speed of sound in the matching medium ranges from about 1480 m per second (depending on temperature) to about 1600 m per second. This range includes the speed of sound in, for instance, non-skin human biological tissue, which is about 1540 m per second.
  • This embodiment has the advantage that the range of the speed of sound in the matching medium matches the speed of sound in non-skin human biological tissue closer than is the case in the previous embodiment.
  • This embodiment has the advantage that the range of the speed of sound in the matching medium ranges from about 1580 m per second (depending on temperature) to about 1680 m per second. This range includes the speed of sound in human skin, which is about 1610-1640 m per second.
  • This embodiment has the advantage that the range of the speed of sound in the matching medium matches the speed of sound in human skin even closer than is the case in the previous embodiment.
  • This embodiment has the advantage that the range of the speed of sound in the matching medium matches the speed of sound in human skin even closer than is the case in the previous embodiment.
  • This embodiment has the advantage that propylene glycol provides an alternative to the use of glycerin.
  • a further embodiment of the matching medium according to the invention wherein the matching medium comprises latex wherein the matching medium comprises latex.
  • This embodiment has the advantage that latex is suitable as an optical matching medium and that the speed of sound in latex is about 1550 m per second (depending on temperature). Without any additional measures, this value is already close to the speed of sound in biological tissue, which is about 1540 m per second.
  • This embodiment has the advantage that salinated water can be used to adjust the speed of sound of the matching medium as determined by the latex comprised in the matching medium to the value of the speed of sound in the turbid medium.
  • This embodiment has the advantage that salinated water can be used to adjust the speed of sound of the matching medium as determined by the mixture comprised in the matching medium to the value of the speed of sound in the turbid medium.
  • a system for imaging an interior of a turbid medium comprises: a light source for generating optical energy to be coupled into the turbid medium; - an ultrasound source for generating ultrasound energy to be coupled into the turbid medium; a matching medium according to any one of the previous embodiments.
  • a system for imaging an interior of a turbid medium would benefit from a matching medium according to the invention according to any one of the previous embodiments.
  • a medical image acquisition system according to the invention comprises: a light source for generating optical energy to be coupled into the turbid medium; an ultrasound source for generating ultrasound energy to be coupled into the turbid medium; a matching medium according to any one of the previous embodiments.
  • a medical image acquisition system would benefit from a matching medium according to the invention according to any one of the previous embodiments.
  • a method of imaging an interior of a turbid medium comprising the following steps: coupling optical energy from a light source into the turbid medium; coupling ultrasound energy from an ultrasound source into the turbid medium, wherein, in at least one of the steps of coupling optical energy and ultrasound energy into the turbid medium, the energy is conducted from at least the source to the turbid medium through use of a matching medium according to any one of the previous embodiments.
  • Use of a matching medium according to any one of the previous embodiments has the advantage that a single matching medium can be used for both the optical and the ultrasound measurement modality.
  • a method for obtaining a matching medium comprising the following steps: checking whether the matching medium has an inverse attenuation distance K for diffuse light, with 40 ⁇ K ⁇ 250 m "1 checking whether the matching medium has an optical scattering coefficient ⁇ ' s , with 100 ⁇ ⁇ ' s ⁇ 5000 m "1 - checking whether the matching medium has an optical absorption coefficient ⁇ a , with ⁇ a ⁇ 250 m "1 in accordance with checking whether the matching medium has an acoustic speed of sound v s , with 1500 ⁇ v s ⁇ 1680 m/s - checking whether the matching medium has an acoustic attenuation a ac , with 0
  • the physical characteristics of a substance forming a potential multimodality matching medium or a component thereof can be looked up in textbooks, databases, etc. Suitability for use in direct contact with human skin can be determined using, for instance, the regulations of the United States' Food and Drug Administration.
  • the invention lies in the realisation that a substance or a combination of substances having the above-mentioned characteristics is suitable as a multimodality matching medium for both optically and acoustically coupling a turbid medium to its surroundings.
  • Such a multimodality matching medium is useful in, for instance, imaging an interior of a female breast using diffuse optical tomography and ultrasound technology.
  • An already useful method comprises the following steps of checking whether the multimodality matching medium: has an inverse attenuation distance K for diffuse light, with 60 ⁇ K ⁇ 150 m "1 - has an optical scattering coefficient ⁇ ' s , with 500 ⁇ ⁇ ' s ⁇ 2000 m "1 has an optical absorption coefficient ⁇ a , with ⁇ a ⁇ 100 m "1 in accordance with has an acoustic speed of sound v s , with 1500 ⁇ v s ⁇ 1580 m/s or with 1580 ⁇ v s ⁇ 1680 m/s - has an acoustic attenuation a ac , with 0 ⁇ a ac ⁇ 10 dB/cm-MHz.
  • This embodiment has the advantage that a matching medium according to this embodiment can be used in direct contact with human skin. This is beneficial if, for instance, the matching medium is used in imaging an interior of a female breast.
  • the advantage of this embodiment is similar to the advantage of the embodiment of the matching medium according to the invention characterized in that the matching medium as a viscosity v ⁇ v max .
  • the matching medium as a viscosity v ⁇ v max .
  • FIG. 1 schematically shows an embodiment of a method for obtaining a multimodality matching medium for use in ultrasound and diffuse optical tomography measurements
  • Fig. 2 schematically shows the speed of sound of a multimodality matching medium as a function of the mass percentage of glycerin comprised in the medium for two temperatures;
  • Fig. 3 schematically shows the speed of sound of a number of fluids
  • Fig. 4 schematically shows the use of a multimodality matching medium in imaging an interior of a female breast
  • Fig. 5 schematically shows an embodiment of a system for imaging an interior of a turbid medium according to the invention
  • Fig. 6 schematically shows a medical image acquisition system according to the invention.
  • Fig. 1 schematically shows an embodiment of a method for obtaining a multimodality matching medium for use in ultrasound and diffuse optical tomography measurements.
  • a multimodality matching medium To be useful as a matching medium suitable for use in imaging in interior of, for instance, a female breast, a multimodality matching medium must have an inverse attenuation distance K, with 40 ⁇ K ⁇ 250 m "1 . The diffuse absorption distance of female breasts typically lies within this range.
  • the check of whether or not the value of the inverse attenuation distance of a potential multimodality matching medium lies within the proper range is carried out in step 5.
  • the inverse attenuation distance K equals V (3 ⁇ a ⁇ ' s ), with ⁇ a being the optical absorption coefficient and with ⁇ ' s being the optical scattering coefficient.
  • a single value for the inverse attenuation distance can be achieved with a plurality of combinations of values of the optical absorption coefficient and the optical scattering coefficient.
  • the two extremes of possible combinations are formed by combining a high value for the optical absorption coefficient with a relatively low value for the optical scattering coefficient or by combining a relatively low value for the optical absorption coefficient with a high value for the optical scattering coefficient.
  • the value of the optical absorption coefficient should be smaller than or equal to 250 m "1 .
  • the check of whether or not the value of the inverse attenuation distance of a potential multimodality matching medium lies within the proper range is carried out in step 10.
  • the value of the optical scattering coefficient ⁇ ' s should comply with the condition that 100 ⁇ ⁇ ' s ⁇ 5000 m "1 . In fig. 1 compliance with this condition is checked in step 15.
  • a potential matching medium To be suitable as a multimodality matching medium capable of efficiently coupling acoustic energy into human tissue, such as a female breast, a potential matching medium must have a speed of sound substantially equal to the speed of sound in human tissue.
  • the speed of sound in human tissue v s complies with the condition that 1500 ⁇ v s ⁇ 1680 m/s. In fig. 1 compliance with this condition is checked in step 20. If the potential multimodality matching medium is viscous its viscosity should not be so high that its use gives rise to gas bubbles being trapped within the potential matching medium.
  • the viscosity of a potential matching medium should not exceed a maximum value.
  • This check is performed in step 25.
  • the acoustic attenuation a ac should be limited. Consequently, the acoustic attenuation should comply with the condition that 0 ⁇ a ac ⁇ 10 dB/cm-MHz. Compliance with this condition is checked in step 30.
  • a potential multimodality matching medium suitable for use in imaging an interior of a turbid medium such as a female breast should be suitable for use in direct contact with human skin.
  • the United States' Food and Drug Administration has issued regulations. Such regulations are be used in step 35 to determine whether or not a potential multimodality matching medium is suitable for use in direct contact with human skin.
  • a potential multimodality matching medium may be made up of a number of components. Not all components need to satisfy all conditions listed in fig. 1. Instead, the conditions listed in fig. 1 can be used as guidelines in relation to potential components of a potential multimodality matching medium.
  • a potential multimodality matching medium may be made up of two components both of which do not satisfy the condition set for the acoustic speed of sound.
  • the medium resulting from combining the two components may have an acceptable speed of sound. This can be the case, for instance, if the acoustic speed of sound of one component is too low and if the acoustic speed of sound of the other component is too high in such a way the acoustic speed of sound of the total satisfies the condition for the acoustic speed of sound shown in fig. 1.
  • a component having a suitable optical absorption coefficient may be combined with another component that has no significant absorption at all.
  • the first component can then be used to ensure that the optical absorption coefficient of the combined total is acceptable, while the second component, that does not interfere with the optical absorption characteristics of the first component, can be used to ensure that a further condition, for instance the condition relating to the acoustic speed of sound, is met.
  • a further condition for instance the condition relating to the acoustic speed of sound.
  • Fig. 2 schematically shows the speed of sound of a multimodality matching medium as a function of the mass percentage of glycerin comprised in the medium for two temperatures. Plotted vertically is the speed of sound in meters per second. Plotted horizontally is the mass percentage of glycerin comprised in the multimodality matching medium.
  • the multimodality matching medium for which the speed of sound is shown in fig. 2 comprises a first component being an optical matching medium and a second component being an acoustic adapter in the form of glycerin.
  • the optical matching medium is a water- based fluid comprising titanium dioxide particles having a diameter of 0.3 ⁇ m suspended in it in order to achieve the appropriate optical scattering coefficient.
  • the optical matching medium itself has a speed of sound of approximately 1490 m per second, which corresponds to the speed of sound in water.
  • the speed of sound in human tissue lies between 1500 and 1680 m per second.
  • the speed of sound of the skin of the breast is about 1610-1640 m per second
  • the speed of sound of the tissue inside the breast is about 1540 m per second
  • the speed of sound of the optical matching medium has to be raised to about 1610-1640 m per second for matching the medium to human skin, or to about 1540 m per second on average for matching the medium to non-skin human tissue.
  • raising the speed of sound to the preferred value of about 1540 m per second can be achieved by mixing in approximately 10% by weight of glycerin.
  • a similar amount of propylene glycol may be used.
  • Raising the speed of sound to the preferred value of about 1610-1640 m per second can be achieved by mixing in approximately 30%-40% by weight of glycerin or a similar amount of propylene glycol.
  • the speed of sound in a medium depends on temperature.
  • Line 40 in fig. 2 has been measured at a temperature of 30 0 C.
  • Line 45 in fig. 2 has been measured at a temperature of 19.8°C.
  • This temperature range illustrates the temperature range that is typically of interest when imaging an interior of a female breast. Patients will probably experience matching mediums having a temperature significantly lower than 20 0 C as being too cold, whereas they will probably experience a temperature significantly higher than 30 0 C as being too hot.
  • Fig. 3 schematically shows the speed of sound of a number of fluids. Plotted vertically is the speed of sound in meters per second. Plotted horizontally is the mass percentage of glycerin comprised in the various fluids.
  • Fig. 3 comprises the lines 40 and 45 shown in fig. 2. Both lines relate to a mixture of a water-based optical matching medium mixed with glycerin. Lines 400 and 450 have been taken from Landolt-B ⁇ rnstein, Molecular Acoustics, Numerical Data and Functional Relationships in Science and Technology, volume 5, Springer, 1967, p. 100 and p. 104. Both line 400 and line 450 relate to a mixture of water and glycerin.
  • lines 40, 45, 400, and 450 may be compared to gain insight into the speed of sound in water-based mixtures as a function of the mass percentage of glycerin comprised in the mixtures.
  • Line 400 has been measured at 30 0 C and line 450 has been measured at 20 0 C.
  • Also shown in fig. 3 are three target values for the speed of sound in the fluids.
  • Target 1 indicated by the number of 460, illustrates the speed of sound in non-skin human tissue, which is about 1540 m per second.
  • Target 2 indicated by the number 470, and target 3, indicated by the number 480, illustrate the speed of sound in human skin, which is about 1610-1640 m per second.
  • Fig. 4 schematically shows the use of a multimodality matching medium in imaging an interior of a female breast.
  • a cup 300 for accommodating an object to be investigated, for instance, a female breast 305.
  • the breast 305 comprises skin 310 and an inner volume 315.
  • the volume inside the cup 300 that is not occupied by the breast 305 is filled with a multimodality matching medium 100.
  • the speed of sound in the multimodality matching medium 100 lies within the range of 1580 m per second to 1680 m per second and is, for instance, about 1625 m per second. This speed corresponds to the speed of sound in human skin.
  • the speed of sound in the inner volume 315 is about 1540 m per second.
  • the cup 300 comprises an ultrasound transducer 325 for generating ultrasound energy in the form of ultrasound waves to be coupled into the breast 305.
  • Means for optically imaging the breast 305 may be present, but are not shown in fig. 4.
  • Matching the speed of sound of the multimodality matching medium 100 to the speed of sound in the skin 310 instead of to the speed of sound in the inner volume 315 that is to be imaged is beneficial because of the following.
  • ultrasound waves generated by the ultrasound transducer 325 will cross from the multimodality matching medium 100 into the skin 310 with limited boundary effects, such as reflections, because, from a speed of sound point of view, the multimodality matching medium 100 and the skin 310 form essentially one medium.
  • Boundary effects being limited is also true for ultrasound waves that substantially graze the skin 310 in the areas 330 and that would otherwise, at least partially, be reflected by the skin 310 into the volume occupied by the multimodality matching medium 100. Such a reflection is indicated by the arrows 335 and 340.
  • ultrasound waves generated by the ultrasound transducer 325 will be diffracted towards a surface normal at the interface between the skin 310 and the inner volume 315.
  • Such a diffraction into the inner volume 315 is indicated by the arrows 335 and 345.
  • ultrasound waves can reach a larger part of the inner volume 315 than would be possible if the speed of sound of the multimodality matching medium 100 were matched to the speed of sound of the inner volume 315.
  • Fig. 5 schematically shows an embodiment of a system for imaging an interior of a turbid medium according to the invention.
  • the system 50 comprises a light source 55, a photodetector unit 60, a receiving volume 65 bound by a receptacle 70, said receptacle 70 comprising a plurality of entrance positions for light 75a and exit positions for light 75b, and light guides 80a and 80b coupled to said entrance positions for light and exit positions for light.
  • the system 50 further includes a selection unit 85 for coupling the input light guide 90 to a number of entrance positions for light and exit positions for light selected from the plurality of entrance positions for light 75a in the receptacle 70.
  • the system 50 comprises further still an ultrasound transducer 105 for generating ultrasound waves to be coupled into the receiving volume 65 and for detecting ultrasound waves returning from the receiving volume 65 after having been coupled into the receiving volume 65. Further still the system 50 also comprises an image reconstruction unit 110 for reconstructing images of an interior of the turbid medium 95. For the sake of clarity, entrance positions for light 75 a and exit positions for light 75b have been positioned at opposite sides of the receptacle 70. In reality, however, both types of positions may be distributed around the receiving volume 65. A turbid medium 95 is placed inside the receiving volume 65.
  • the turbid medium 95 is then irradiated with light from the light source 55 from a plurality of positions by coupling the light source 55 using the selection unit 85 to successively selected entrance positions for light 75a.
  • the light is chosen such that it is capable of propagating through the turbid medium 45.
  • Light emanating from the receiving volume 65 as a result of irradiating the turbid medium 95 is detected from a plurality of positions using exit positions for light 75b and using photodetector unit 60. The detected light is then used to derive an image of an interior of the turbid medium 95.
  • Deriving an image of an interior of the turbid medium 95 based on the detected light is possible as at least part of this light has traveled through the turbid medium 95 and, as a consequence, contains information relating to an interior of the turbid medium 95.
  • the light was intentionally chosen such that it is capable of propagating through the turbid medium 95.
  • the turbid medium 95 is also irradiated with ultrasound waves generated by the ultrasound transducer 105. This irradiation with ultrasound waves may take place simultaneously with the irradiation of the turbid medium 95 with light from the light source 55. However, this is not necessarily so and irradiation of the turbid medium 95 with ultrasound waves may take place while the turbid medium 95 is not irradiated with light from the light source 55.
  • Ultrasound waves detected using the ultrasound transducer 105 are used to derive an image of an interior of the turbid medium 95.
  • This image may be an ultrasound image, but also a multimodality image based on both detected light and detected ultrasound waves.
  • the image may be a combined ultrasound and optical image (possibly comprising an overlay of an ultrasound and an optical image), an optical image during the reconstruction of which use was made of the detected ultrasound waves (for instance for detecting the boundary of the turbid medium 95), or an ultrasound image during the reconstruction of which use was made of the detected light.
  • the turbid medium 95 is at least partially surrounded by a multimodality matching medium 100 having optical characteristics, such as, for instance, the absorption coefficient and the scattering coefficient, and ultrasound characteristics that substantially match the corresponding optical and ultrasound characteristics of the turbid medium 95 for the wavelengths of light and for the ultrasound waves used for imaging an interior of the turbid medium 95.
  • a multimodality matching medium is described with reference to fig. 2.
  • the multimodality matching medium 100 has optical and ultrasound characteristic that substantially match to corresponding characteristics of the turbid medium 95, the optical and ultrasound coupling of the turbid medium 95 to its surroundings is improved as compared to a situation without a multimodality matching medium 100.
  • the multimodality matching medium 100 optical boundary effects, such as reflections occurring at the boundary of the turbid medium 95 are reduced. Moreover, optical short-circuits around the turbid medium 95 in the receiving volume 65 are prevented. Moreover still, the multimodality matching medium 100 improves the coupling of ultrasound energy into and out of the turbid medium 95.
  • the receiving volume 65 is bound by a receptacle 70.
  • the receptacle 70 may have a cup light geometry.
  • a receptacle having a parallel plate geometry may be used.
  • Another embodiment of a system for imaging an interior of a turbid medium is that of a handheld device that may, for instance, be pressed against a side of a turbid medium.
  • the measurement volume (not bound by a receptacle) is the volume occupied by the part of the turbid medium from which light is detected as a result of irradiating the turbid medium.
  • the multimodality matching medium may then be accommodated between the handheld device and the side of the turbid medium against which the device is pressed.
  • Fig. 6 schematically shows a medical image acquisition system according to the invention.
  • the medical image acquisition system 180 comprises the system 50 discussed in fig. 4 as indicated by the dashed square.
  • the medical image acquisition system 180 further comprises a screen 185 for displaying an image of an interior of the turbid medium 95 and an input interface 190, for instance, a keyboard enabling and operated to interact with the medical image acquisition system 180.

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Abstract

L'invention porte sur un milieu d'adaptation qui est utilisé pour coupler optiquement un milieu optiquement trouble à son environnement pendant des mesures par tomographie optique diffuse. De manière générale, un milieu d'adaptation optique rend difficile de coupler acoustiquement le milieu trouble à son environnement de manière efficace. Selon l'invention, ce problème est résolu à l'aide d'un milieu d'adaptation qui adapte les caractéristiques à la fois optiques et acoustiques du milieu trouble aux caractéristiques optiques et acoustiques de l'environnement du milieu trouble. L'invention explique la façon dont un milieu d'adaptation multimodal qui couple à la fois optiquement et acoustiquement un tissu humain à son environnement peut être obtenu.
PCT/IB2008/052910 2007-07-25 2008-07-21 Milieu d'adaptation multimodal pour des mesures par tomographie optique diffuse et ultrasons Ceased WO2009013692A2 (fr)

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Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2009081321A1 (fr) * 2007-12-18 2009-07-02 Koninklijke Philips Electronics N.V. Partie réceptrice destinée à recevoir un milieu trouble et pourvue d'un revêtement
US9770521B2 (en) 2012-05-09 2017-09-26 Sinvent As Ultrasound contact fluid
US20180275052A1 (en) * 2017-03-27 2018-09-27 Ecolab Usa Inc. Techniques and materials for calibrating optical sensors

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN106124627B (zh) * 2016-08-01 2019-03-19 上海市计量测试技术研究院 一种声散射系数现场测试用传声器线阵

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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB2102657B (en) * 1981-07-24 1985-07-03 Nat Res Dev Ultrasonic transducers
US4542745A (en) * 1983-06-27 1985-09-24 Technicare Corporation Ultrasonic emulsion fluids

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2009081321A1 (fr) * 2007-12-18 2009-07-02 Koninklijke Philips Electronics N.V. Partie réceptrice destinée à recevoir un milieu trouble et pourvue d'un revêtement
US9770521B2 (en) 2012-05-09 2017-09-26 Sinvent As Ultrasound contact fluid
US20180275052A1 (en) * 2017-03-27 2018-09-27 Ecolab Usa Inc. Techniques and materials for calibrating optical sensors
US10794826B2 (en) * 2017-03-27 2020-10-06 Ecolab Usa Inc. Techniques and materials for calibrating optical sensors

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